Monitoring physiological condition and detecting abnormalities

ABSTRACT

A system for monitoring an individual&#39;s physiological condition and detecting abnormalities therein, comprising concurrently receiving at least a first signal and a second signal. The first and second signals are conditioned to minimize background extraneous noise after which, each signal is concurrently processed and analyzed to detect repeating cyclical patterns and further characterized to identify individual components of the repeating cycles. At least one individual component in one signal is selected as a reference marker for a selected component in the other signal. The two signals are then synchronized, outputs produced therefrom and stored in a database. The system is provided with a plurality of devices for acquiring, transmitting and conditioning at least two physiological signals, a software program cooperable with a microprocessor configured for receiving said transmitted signals and conditioned signals, and processing said signals to characterize and synchronize said signals and provide signal outputs derived therefrom, a database for storing said transmitted signals, conditioned signals, synchronized signals, and output signals derived therefrom. The output signals are useful for reporting and optionally for retransmission to the individual&#39;s body and providing physiologically stimulatory signals thereto.

FIELD OF THE INVENTION

This invention relates to monitoring cardiovascular health. Moreparticularly, this invention relates to systems and methods for earlydetection of cardiovascular abnormalities and malfunctions.

BACKGROUND OF THE INVENTION

Numerous types of malfunctions and abnormalities that commonly occur inthe cardiovascular system, if not diagnosed and appropriately treated orremedied, will progressively decrease the body's ability to supplysufficient oxygen to satisfy the coronary oxygen demand when theindividual encounters stress. The progressive decline in thecardiovascular system's ability to supply oxygen under stress conditionswill ultimately culminate in a heart attack, i.e., myocardial infarctionevent that is caused by the interruption of blood flow through the heartresulting in oxygen starvation of the heart muscle tissue (i.e.,myocardium). In serious cases, the consequences are mortality while inless serious cases, permanent damage will occur to the cells comprisingthe myocardium that will subsequently predispose the individual'ssusceptibility to additional myocardial infarction events.

In addition to potential malfunctions and abnormalities associated withthe heart muscle and valve tissues (e.g., hypertrophy), the decreasedsupply of blood flow and oxygen supply to the heart are often secondarysymptoms of debilitation and/or deterioration of the blood flow andsupply system caused by physical and biochemical stresses. While some ofthese stresses are unavoidable, e.g., increasing age, heredity andgender, many of the causative factors of cardiovascular diseases andmalfunction are manageable, modifiable and treatable if theirdebilitating effects on the cardiovascular system are detected earlyenough. Examples of such modifiable risk factors include high bloodpressure, management of blood cholesterol levels, Diabetes mellitus,physical inactivity, obesity, stress, and smoking. Examples ofcardiovascular diseases that are directly affected by these types ofstresses include atherosclerosis, coronary artery disease, peripheralvascular disease and peripheral artery disease. In many patients, thefirst symptom of ischemic heart disease (IHD) is myocardial infarctionor sudden death, with no preceding chest pain as a warning.

Screening tests are of particular importance for patients with riskfactors for IHD. The most common initial screening test for IHD is tomeasure the electrical activity over a period of time which isreproduced as a repeating wave pattern, commonly referred to as anelectrocardiograph (ECG), showing the rhythmic depolarization andrepolarization of the heart muscles. Analysis of the various waves andnormal vectors of depolarization and repolarization yields importantdiagnostic information. However, ECG measurements are not particularlysensitive nor are the data very useful for detecting cardiovascularabnormalities or malfunctions. Therefore, stressing the heart undercontrolled conditions and measuring changes in the ECG data is usually,but not always, the next step. The stresses may be applied by theperformance of physical exercise or alternatively, by administration ofpharmaceutical compounds such as dobutamine, which mimic thephysiological effects of exercise. Other screening tests for IED includethe radionucleotide stress test which involves injecting a radioactiveisotope (typically thallium or cardiolyte) into a patient's bloodstream,then visualizing the spreading of the radionucleotide throughout thevascular system and its absorption into the heart musculature. Thepatient then undergoes a period of physical exercise after which, theimaging is repeated to visualize changes in distribution of theradionucleotide throughout the vascular system and the heart. Stressechocardiography involves ultrasound visualization of the heart before,during and after physical exercise. The radionucleotide stress test andstress echocardiography are often used in combination with ECGmeasurements in order to gain a clearer understanding of the state ofindividual's cardiovascular health.

However, there are a number of serious limitations associated with theuse of ECG and related stress tests for detecting abnormalities andmalfunctions that are indicators of ischemic heart disease. ECGprintouts provide a static record of a patient's cardiovascular functionat the time the testing was done, and may not reflect severe underlyingheart problems at a time when the patient is not having any symptoms.The most common example of this is in a patient with a history ofintermittent chest pain due to severe underlying coronary arterydisease. This patient may have an entirely normal ECG at a time when heis not experiencing any symptoms despite the presence of an underlyingcardiac condition that normally would be reflected in the ECG. In suchinstances, the ECG as recorded during an exercise stress test may or maynot reflect an underlying abnormality while the ECG taken at rest may benormal. Furthermore, many abnormal patterns on an ECG may benon-specific, meaning that they may be observed with a variety ofdifferent conditions. They may even be a normal variant and not reflectany abnormality at all. Routine exercise ECG is not recommended inpatients who have no signs or symptoms of coronary artery disease.Exercise ECG is notoriously ineffective at predicting underlyingcoronary artery disease, and a positive exercise ECG test in anapparently healthy patient is not known to have any association withcardiovascular morbidity and mortality.

Ballistocardiography (BCG) is a non-invasive method of graphicallyrecording minute movements on an individual's body surface as aconsequence of the ballistic i.e., seismic forces associated withcardiac function, e.g., myocardial contractions and related subsequentejections of blood, ventricular filling, acceleration, and decelerationof blood flow through the great vessels. These minute movements areamplified and translated by a pick-up device (e.g., an accelerometer)placed onto a patient's sternum, into signals with electrical potentialsin the 1-20 Hz frequency range and recorded on moving chart paper. Therhythmic contractions of the heart and related flows of blood within andfrom the heart's chambers under resting and stressed conditions producerepeating BCG wave patterns that enable visual detection and assessmentby qualified diagnosticians of normal and abnormal cardiovascularfunction. The BCG records the vigor of cardiac ejection and the speed ofdiastolic filling. It provides a practical means of studying thephysiologic response of the heart in its adjustment to the stress ofexercise. The application of the light BCG exercise test to subjectswithout clinical or ECG evidence of heart disease, or to hypertensivesubjects, or to patients with coronary artery disease and to thosesuspected of having myocarditis, provides information or clinicalimportance which cannot be obtained from any other means of physicaldiagnosis or from the BCG at rest (Mandelbaum et al., 1954. Circulation9:388-399). The most common BCG wave pattern classification system isknown as the Starr system (Starr et al., 1961, Circulation 23: 714-732)and identifies four categories of cardiovascular function depending onthe abnormalities in the measured BCG signals. In class 1, all BCGcomplexes are normal in contour. In class 2, the majority of thecomplexes are normal, but one or two of the smaller complexes of eachrespiratory cycle are abnormal in contour. In class 3, the majority ofthe complexes are abnormal in contour, usually only a few of the largestcomplexes of each respiratory cycle remaining normal and in class 4,there is such complete distortion that the waves cannot be identifiedwith confidence, and the onset of ejection could not be located withoutthe assistance of a simultaneous ECG (Starr, 1964, J. Am. Med. Assoc.187:511). In general, a normal healthy person should belong to Starrclass 1, and person belonging to class 3 or 4 has a significantabnormality in one or more components of the cardiovascular system.However, the classification is not exact, as it is done visually anddepends on the person making the classification (Starr, 1964, J. Am.Med. Assoc. 187:511).

Coronary angiography enables visualization and assessment of potentialcardiovascular abnormalities and malfunctions that are not possible todetect with the afore-mentioned stress tests, including as occlusions,stenosis, restenosis, thrombosis, aneurismal enlargement of coronaryartery lumens, heart chamber size, heart muscle contraction performanceand heart valve function. During a coronary angiogram, a small catheteris inserted through the skin into an artery in either the groin or thearm. Guided with the assistance of a fluoroscope, the catheter is thenadvanced to the opening of the coronary arteries, the blood vesselssupplying blood to the heart. Next, a small amount of radiographiccontrast solution is injected into each coronary artery. The images thatare produced are called the angiogram. Although angiographic imagesaccurately reveal the extent and severity of all coronary arterialblockages and details of the heart musculature, the procedure isinvasive and requires the use of local anaesthesia and intravenoussedation.

SUMMARY OF THE INVENTION

The exemplary embodiments of the present invention, at least in someforms, provide systems, methods, devices, apparatus and softwareprograms for acquiring, processing, synchronizing, storing and reportingat least two physiologically generated signals useful for monitoring thephysiological condition of a mammalian system and for detectingabnormalities therein.

According to one exemplary embodiment, there is provided a systemconfigured for monitoring the cardiovascular condition of a mammalianbody. The system is provided with at least: (a) a plurality of devicesconfigured to concurrently detect, acquire and transmit at least twodifferent types of physiological signals produced by the cardiovascularsystem, (b) an analog-digital converter for converting the signals intodigital data that can be processed and stored, (c) at least oneapparatus configured to receive therethrough and condition the at leasttwo signals, (d) a microprocessor suitably configured with hardware, anoperating system and software provided for concurrently processing,analyzing, characterizing, reporting and transmitting said physiologicaland said conditioned signals, (e) a software program configured toconcurrently process said conditioned signals to at least firstly detectrepeating cyclical patterns in the conditioned signals, secondly toidentify and characterize individual components comprising the repeatingcycles, thirdly to identify a first reference component in at a firstconditioned signal and a second reference signal in a second conditionedsignal, fourthly to synchronize at least a first conditioned signal witha second conditioned signal by aligning the first and second referencepoints, and then subsequently aligning the repeating cyclical pattern ofthe first conditioned signal with the repeating cyclical pattern of thesecond conditioned signal in constant reference to the first and secondreference points, and fifthly producing at least a synchronized pairedsignal derived therefrom, and a database provided for communicating andcooperating with the microprocessor for storing therein and providingtherefrom the physiological signals, conditioned signals, synchronizedsignals and signal outputs derived therefrom.

According to one aspect, there is provided a plurality of devicesconfigured for concurrently detecting, acquiring and transmitting atleast two physiological signals from a cardiovascular system. Exemplarysuitable signals include electrical signals, electronic signals, seismicsignals, mechanical signals, acoustic signals, imaging signals and thelike. Suitable devices are exemplified by electrocardiographs,ballistocardiographs, seismocardiographs, angiographs and the like.Additional physiological monitoring equipment and instrumentsexemplified by pulsoximeters and blood pressure measuring devices, maybe optionally provided to cooperate with said devices. The signals maybe transmitted by wires or by wireless means.

According to another aspect, there is provided a filtering apparatusconfigured to remove extraneous noise components from the digitalsignals converted from the physiological signals acquired from themammalian cardiovascular system thereby providing at least twoconditioned signals.

According to exemplary embodiment of the present invention, there isprovided at least one software program configured to concurrentlyperform a plurality of the following functions on the at least twoconditioned signals: (a) process, (b) analyze, (c) optimize, (d)transform, (e) identify repeating cyclical patterns, (f) identify andcharacterize individual components of the repeating cyclical patterns,(g) identify a reference component in each of the cyclical patternscomprising each of the conditioned signals, (h) synchronize at least twoof the conditioned signals by aligning the reference component of afirst conditioned signal with the reference component of the secondconditioned signal, (i) generate output comprising at least onesynchronized signal wave pattern, (j) report identifying andcharacterizing key components of the at least one synchronized signalwave pattern relating to a physiological condition, (k) store, and (k)re-transmit the synchronized signals. It is within the scope of thisinvention for the synchronized signals to be transmitted back to themammalian system for providing a stimulatory signal thereto.

According to one aspect, the software program is suitably configured forprocessing, comparing and reporting a plurality of synchronized signals,and providing outputs therefrom.

According to another aspect, the software program may comprise aplurality of mathematical algorithms, or alternatively heuristicalgorithms, or optionally, a combination of mathematical and heuristicalgorithms.

According to another exemplary embodiment of the present invention,there is provided a database for storing therein and providing therefroma plurality of synchronized signals produced as disclosed herein.

According to one aspect, the database may be provided as an integralcomponent of the microprocessor provided herein.

According to another aspect, the database may be contained in a facilityprovided for such purposes. The database is configured receive thereinpluralities of synchronized signals produced as disclosed herein. Thesynchronized signals may be delivered to and transmitted from thedatabase base electrically, electronically, acoustically, via beams oflight, and the like using wired or alternatively wireless transmissionmethods.

BRIEF DESCRIPTION OF THE DRAWINGS

The present invention will be described in conjunction with reference tothe following drawing, in which:

FIG. 1 is a cross-sectional perspective view of the heart showing thetricuspid and mitral valves in opened positions, and the pulmonary andaortic valves in closed positions;

FIG. 2 is a cross-sectional perspective view of the heart showing thetricuspid and mitral valves in closed positions, and the pulmonary andaortic valves in opened positions;

FIG. 3 is a schematic diagram showing the relationships between therhythmic electrical functions and related physical motions of aphysiologically normal heart cooperating with a physiologically normalcardiovascular system, with reference to: (a) electrocardiographic (ECG)events, (b) systolic and diastolic periods of time, (c) blood pressureduring the systole and diastole periods, and (d) ballistocardiographic(BCG) events;

FIG. 4 is an exemplary chart showing the traditional Starr BCG signalclassification system;

FIG. 5 is a schematic diagram showing an exemplary system of the presentinvention configured for concurrently detecting and transmitting ECG andBCG signals produced by a heart to a device configured to synchronizeone of the signals and provide a visual output of the synchronized ECGand BCG signals;

FIG. 6 is an flow chart of one embodiment of the present inventionshowing an exemplary method for processing and synchronizingconcurrently produced ECG and BCG signals;

FIG. 7 is a graph illustrating a prior art curve-length concept;

FIG. 8 is a systems flow chart showing the data flow into and out of thegraphical user interface;

FIG. 9 is an exemplary illustration of a layout for an ECG-BCG analysisGraphical User Interface (GUI) according to one aspect of the presentinvention;

FIG. 10 is an exemplary illustration of a basic layout for a databaseaccording to one aspect of the present invention;

FIG. 11 is an exemplary illustration of a sample SQL data tableaccording to one aspect of the present invention;

FIG. 12 a shows a raw unconditioned and unsynchronized ECG-BCG signalset of a healthy individual with a well-functioning cardiovascularsystem, collected during a resting stage prior to exercising, while FIG.12 b shows a raw unconditioned and unsynchronized ECG-BCG signal setcollected from the healthy individual during the post-exercise period.

FIG. 13 a shows the resting stage ECG-BCG signal set from FIG. 12 aafter conditioning and synchronization according to one aspect of thepresent invention, FIG. 13 b shows the post-exercise ECG-BCG signal setfrom FIG. 12 b after conditioning and synchronization, and FIG. 13 cshows the synchronized post-exercise BCG signal overlaid onto thesynchronized pre-exercise resting-stage BCG signal;

FIG. 14 a shows a raw unconditioned and unsynchronized ECG-BCG signalset of an unhealthy individual with a somewhat debilitatedcardiovascular system, collected during a resting stage of prior toexercising, while FIG. 14 b shows a raw unconditioned and unsynchronizedECG-BCG signal set collected from the unhealthy individual during thepost-exercise period.

FIG. 15 a shows the resting stage ECG-BCG signal set from FIG. 14 aafter conditioning and synchronization according to one aspect of thepresent invention, FIG. 15 b shows the post-exercise ECG-BCG signal setfrom FIG. 14 b after conditioning and synchronization, and FIG. 15 cshows the synchronized post-exercise BCG signal overlaid onto thesynchronized pre-exercise resting-stage BCG signal;

FIG. 16 a shows a raw unconditioned and unsynchronized ECG-BCG signalset of an at-risk individual with a seriously debilitated cardiovascularsystem, collected during a resting stage prior to exercising, while FIG.16 b shows a raw unconditioned and unsynchronized ECG-BCG signal setcollected from the at-risk individual during the post-exercise period;

FIG. 17 a shows the resting stage ECG-BCG signal set from FIG. 16 aafter conditioning and synchronization according to one aspect of thepresent invention, FIG. 17 b shows the post-exercise ECG-BCG signal setfrom FIG. 16 b after conditioning and synchronization, and FIG. 17 cshows the synchronized post-exercise BCG signal overlaid onto thesynchronized pre-exercise resting-stage BCG signal; and

FIGS. 18 a, 18 b and 18 c are comparisons of the overlaid synchronizedpre- and post-exercise BCG signals for the healthy individual, unhealthyindividual, and at-risk individual respectively.

DETAILED DESCRIPTION OF THE INVENTION

The present invention relates to the detection and monitoring of twodisparate signals associated with rhythmic electrical cardiovascularfunctions and physical movements associated with the beating of anindividual's heart, and the synchronization of a selected signal to theother signal whereby the synchronized signal enables and facilitatesdetection of potential abnormalities and malfunctions associated withthe individual's cardiovascular system. Two exemplary suitable signalsfor monitoring cardiovascular function and for synchronization with eachother are ECG and BCG signals. A brief description follows ofcardiovascular functions as they relate to the generation of ECG and BCGsignals, for reference to during disclosure herein of how either ofthese signals may be synchronized to the other for the detection ofpotential cardiovascular abnormalities and malfunctions according to thepresent invention.

As shown in FIGS. 1 and 2, the heart 10 comprises four chambers, theright atrium 20 interconnected with the right ventrical 30 by thetricuspid valve 35, and the left atrium 40 interconnected with the leftventricle 50 by the mitral valve 45. Blood is delivered into the rightatrium 20 from the upper half of the body via the superior vena cava 15,and from the lower half of the body via the inferior vena cava 17. Thetricuspid valve 25 is opened by concurrent contraction of the rightatrium myocardium (i.e., muscle tissue) and the right ventricularpapillary muscles 27 thereby allowing blood flow from the right atrium20 into the right ventricle 30, and then closes when the papillarymuscles 27 relax. When the myocardium of the right ventricle 30contracts, blood is forced from the right ventricle 30 through thepulmonary valve 35 into the pulmonary artery 37 which delivers the bloodinto the lungs wherein it is oxygenated. The oxygenated blood is thenreturned into the left atrium via pulmonary veins 38 and 39. Theoxygenated blood flows from the left atrium into the left ventricle whenthe mitral valve 45 is opened by concurrent contraction of the leftatrium myocardium and the left ventricular papillary muscles 47 therebyallowing blood flow from the left atrium 40 into the left ventricle 50,and then closed when the papillary muscles 47 relax. The oxygenatedblood is then forced out of the left ventricle 50 through the aorticvalve 55 into the aorta which delivers the oxygenated blood tothroughout the body via the peripheral vascular system.

Every rhythmic ‘beat’ of the heart involves three major stages: atrialsystole, ventricular systole and complete cardiac diastole. Electricalsystole is the electrical activity that stimulates the muscle tissue,i.e., the myocardium of the chambers of the heart to make them contract.Referring to FIG. 3( b), atrial systole 110 is the period of contractionof the heart muscles (i.e., myocarida) encompassing the right and leftatria 20 and 40. Both atria 20 and 40 contract concurrently withpapillary muscle 27 and 47 contraction thereby forcing open thetricuspid valve 25 and the mitral valve 45 as shown in FIG. 1.Electrical systole, i.e. electrical depolarization of the atria 20 and40 begins within the sinoatrial (SA) node located in the right atriumjust below the opening to the superior vena cava. The conductionelectrical depolarization continues to travel in a wave downwards,leftwards and posteriorly through both atria depolarising each atrialmuscle cell in turn. It is this propagation of charge that can be seenas the P wave on an ECG as exemplified in FIG. 3( a). This is closelyfollowed by mechanical systole i.e., mechanical contraction of the atriawhich is detected on a BCG (FIG. 3( d)) as an impact (i.e., “h” peak)and recoil (i.e., “i” valley) wave pattern. As the right and left atria20 and 40 begin to contract, there is an initial high velocity flow ofblood into the right and left ventricles 30 and 50 detectable as the “j”peak on the BCG (FIG. 3( d)). Continuing atrial contraction as thetricuspid valve 25 begins to close forces an additional lower velocityflow of blood into the right and left ventricles 30 and 50. Theadditional flow of blood is called the “atrial kick” and is shown inFIG. 3( d) as the “a—a¹” wave pattern. After the atria are emptied, thetricuspid and mitral valves 25 and 45 close thereby giving rise to thefootward “g” wave pattern on the BCG as shown in FIG. 3( d).

Referring to FIG. 3( b), ventricular systole 120 is the contraction ofthe muscles i.e., myocardia of the left and right ventricles 30 and 50,and is caused the electrical depolarization of the ventricular myocardiagiving rise to the QRS complex in a ECG plot as shown in FIG. 3( a). Thedownward Q wave is caused by the downward flow of depolarisation throughthe septum 33 along a specialized group of cells called “the bundle ofHis”. The R wave is caused by depolarization of the ventricular muscletissue, while S wave is produced by depolarization of the heart tissuebetween the atria 20 and 40 and ventricles 30 and 50. As thedepolarization travels down the septum and throughout the ventricularmyocardia, the atria 20 and 40 and sinoatrial node start to polarise.The closing of the tricuspid and mitral valves 25 and 45 mark thebeginning of ventricular systole and cause the first part of the“lub-dub” sound made by the heart as it beats. Formally, this sound isknown as the “First Heart Tone” and is produced during the period oftime shown in FIG. 3( b) as S₁. As the electrical depolarization of theventricular myocardia peaks, as exemplified by the “R” peak shown inFIG. 3( a), the AV septum 33 separating the right and left ventricles 30and 50 contracts causing an impact, i.e., the “H” peak and a recoili.e., the “I” valley detectable on a BCG as shown in FIG. 3( d). Theventricular contraction forces the blood from the right ventricle 30into the pulmonary artery 37 through the pulmonary valve 35, and fromthe left ventricle 50 into the aorta 60 through the aortic valve 55under very high velocity thereby causing the “J” wave in the BCG asshown in FIG. 3( d). The deceleration of blood flow from the leftventricle 50 into the aorta 60 causes a footward decline in the BCGresulting in the “K” wave (FIG. 3( d). As the left ventricle 50 empties,its pressure falls below the pressure in the aorta 60, and the aorticvalve 55 closes. Similarly, as the pressure in the right ventricle 30falls below the pressure in the pulmonary artery 37, the pulmonary valve35 closes. The second part of the “lub-dub” sound, i.e., the “SecondHeart Tone” is produced during the period of time shown in FIG. 3( b) asS₂ and is caused by the closure of the pulmonary and aortic valves 35and 55 at the end of ventricular systole thereby giving rise to theheadward “L” wave detectable on a BCG as shown in FIG. 3( d.)Concurrently with the closing of the pulmonary and aortic valves 35 and55, the AV septum 33 relaxes and moves headward, and the ventricularmyocardia is re-polarized giving rise to the “T” wave in thecorresponding ECG as shown in FIG. 3( a).

Cardiac diastole is the period of time when the heart 10 relaxes aftercontraction in preparation for refilling with circulating blood. Atrialdiastole is when the right and left atria 20 and 40 are relaxing, whileventricular diastole is when the right and left ventricles 30 and 50 arerelaxing. Together, they are known as complete cardiac diastole 150 asshown in FIG. 3( b). During the period of atrial diastole, the rightatrium 20 is re-filled by deoxygenated blood returning from the upperhalf of the body via the superior vena cava 15 and from the lower halfof the body via the inferior vena cava 17, while the left atrium isre-filled with oxygenated blood returning from the lungs via pulmonaryveins 38 and 39. Re-filling of the atria 20 and 40 causes a downward “M”wave in the BCG FIG. 3( d) early in diastole which coincides withrepolarization of the bundle of His cells, which is shown as the “U”wave in FIG. 3( a). As the right and left atria 20 and 40 are filled totheir maximum capacities, the reflux of blood against the tricuspidvalve 25 and mitral valve 45 cause an upward “N” wave in the BCG asshown in FIG. 3( d).

In summary, an ECG, as exemplified in FIG. 3( a) provides information onthe rhythmic formation, propagation and regeneration of electricalsignals within the heart muscles wherein: (a) the P wave results fromelectrical depolarization of the right and left atria signalling theonset of atrial systole during which time the right and left atriacontract, (b) the QRS wave pattern results from depolarization of theright and left ventricles signalling the onset of ventricular systoleduring which time the right and left ventricles contract, (c) thesubsequent T wave is produced by electrical repolarization of theventricular myocardia, and (d) the U wave is produced by electricalrepolarization of the bundle of His cells. The T and U waves arenotoriously hard to locate and annotate due to their slow slopes and lowamplitudes.

The BCG, as exemplified in FIG. 3( d), records the vigor of cardiacejection of blood from the atria and ventricles, and the speed offilling of the atrial chambers during the diastolic period. Morespecifically, the BCG provides information on the mechanical functioningand related physical movements of the heart muscles, valves, and relatedflows of blood into, between and out of the atria and ventricles as aconsequence of electrical depolarization and re-polarization of theheart tissues. As the heart pumps blood from the right and left atriavia the right and left ventricles into the pulmonary artery and theaorta, and as the blood flow returns to the left and right atria, recoilpressures in the opposite directions are applied by the body. Thepumping pressures result in headward BCG wave peaks, while the recoilpressures on bloodflow result in the downward BCG wave peaks. The “h-i”wave component of the BCG shows the physical impact and recoil fromdepolarization of the SA node and related atrial movements. The “j-a-a¹”wave pattern records the impact and recoil of the heart in response toblood flow from the atria 20 and 40 into the right and left ventricles30 and 50. The “g” wave pattern is a caused by the closing of thetricuspid and mitral valves 35 and 45. The “H-I” wave pattern is causedby the impact and recoil of the septum 33 and corresponds to theisometric phase of ventricular systole during which time the heart isphysically twisting and moving upward within the chest cavity. The “J-K”wave pattern is caused by the initial highly forceful impact of bloodfrom the right and left ventricles into the pulmonary and aorticarteries (the J peak) followed by deceleration of blood flow in theaorta (the J-K slope). The L wave is caused by the movement of theseptum during isometric relaxation, while the M wave is caused by theflow of blood into the right atrium from the vena cava vessels and intothe left atrium by the pulmonary veins. The heart is physicallyrecoiling and moving downward in the chest cavity during isometricrelaxation. The N wave is caused by impact of blood onto the ventricularmyocardia at the end of early diastolic filling due to reflux.

Considerable energy is generated by the ventricular myocardia duringventricular systole, and the strength of ventricular contraction isfueled by the oxygen in the blood returning from the lungs into the leftventricle via the left atrium. About 80% of the oxygen in the bloodflowing through the left ventricle is removed to supply the ventricularmyocardial oxygen demand during ventricular systole. The cardiovascularsystems of most individuals under “resting” conditions, can supplyadequate amounts of oxygen during coronary perfusion to provide regularrepeating ECG and BCG patterns as exemplified in Fibs 3(a) and 3(d).When healthy individuals are placed under stressed conditions, e.g.,exercise, it is known that as the heart rate increases to providesufficient oxygen to the maintain efficient cardiovascular functionwhile supplying additional oxygen to meet the demands from theperipheral musculature, the related ECG and BCG wave patterns reproducethe typical repeating wave patterns as illustrated in FIGS. 3( a) and3(d) but the slopes and amplitudes of the wave patterns increasesignificantly. However, individuals experiencing some debilitation intheir cardiovascular physiology and function when stressed, tend toproduce BCG signals that show significant variations in their repeatingBCG wave patterns when compared to their BCG produced under “resting”conditions. FIGS. 4( a)-4(d) show four types of exemplary BCG signalsthat are divided into separate classes of cardiovascular abnormalitiesbased on the Starr classification system (Starr, 1964, Journal of theAmerican Medical Association 187: 511). In Class 1 (FIG. 4( a)), all BCGwave patterns are normal in contour. In Class 2 (FIG. 4( b)), themajority of the BCG wave patterns are normal but one or two of thesmaller wave patterns in each respiratory cycle are abnormal. In Class 3(FIG. 4( c)), the majority of the BCG wave patterns are abnormal incontour and usually, only a few of the largest wave patterns of eachrespiratory cycle remain normal. Lastly, in Class 4 (FIG. 4( d)), thereis such complete distortion in the BCG wave patterns that none of thewaves can be identified with confidence, and it is difficult todetermine the onset of each rhythmic cycle. In general, a normal healthyperson should belong to the Starr Class 1 (FIG. 4( a)), while a personproducing BCG wave patterns that fall into the Starr Classed 3 or 4(FIG. 4( c)) or 4(d)) has significant cardiovascular abnormalitiesand/or malfunctions.

We have surprisingly discovered that, regardless of the type of BCG wavepattern produced by an individual under stressed conditions in referenceto the Starr classification system, it is possible to synchronize theindividual's rhythmic BCG pattern with their ECG signal undernon-stressed, i.e., resting stage conditions, and then characterize theindividual's cardiac function by calculating a plurality of thefollowing parameters:

-   -   (1) stroke volume: the amount of blood ejected from the left        ventricle during systole. Stroke volume (SV)=end diastolic        volume (EDV)−end systolic volume (ESV);    -   (2) cardiac output: the volume of blood pumped by the left        ventricle per minute, calculated by multiplying the stroke        volume by the number of heart beats per minute. Cardiac output        (CO)=SV X heart rate (HR measured in beats per minute);    -   (3) ending diastolic volume: the volume of blood contained in        the left ventricle at the end of the rest phase when the left        ventricle is at its fullest;    -   (4) ending systolic volume: the volume of blood left in the left        ventricle at the end of the systolic period when the ventricle        contains its lowest volume;    -   (5) ventricular ejection fraction: the percentage of the ending        diastolic volume that is ejected during each heart beat.        Ejection fraction (EF)=SV/EDV:    -   (6) cardiac output index: the volume of blood pumped by the left        ventricle per minute normalized to the body surface area        (measured in meters²). Cardiac output index (CI)=CO÷body surface        area (BSA)=SV X HR/BSA;    -   (7) Pre-ejection period: The time from the Q-wave peak on the        ECG to the opening of the aortic valve;    -   (8) Cardiac performance index (CPI)=(isovolumetric relaxation        time+isovolumetric contraction time)/Ejection time (ET). The CPI        can also be calculated as the (time period between the I-peak        and the L-peak)/ET. The CPI can also be calculated as the (time        period between aortic valve opened and aortic valve        closed)/(time period between the I-peak and the L-peak).

The quantifications of the above parameters are dependent onsynchronizing, as illustrated in FIGS. 3( a) and 3(d), the R wave peakon an ECG caused by the depolarization of the ventricular muscle tissuewith the H peak on a corresponding BCG which signals the rapid increasein intraventricular pressure caused by the impact of the septum as thedirect consequence of the depolarization of the ventricular musclepressure. Since the H-wave and I-wave on a BCG are caused by the impactand recoil of the septum concurrent with depolarization of theventricular muscle tissue, (a) the time duration of the H-I wave, i.e.,the isovolumetric contraction time, and (b) the distance between the Hand I peaks over the duration of that wave, can be measured. These dataenable calculation of the slope of the H-I wave and the time to maximumvelocity of the blood flow resulting from the ventricular contractionwhich results in rapid blood flow into the aorta thereby causing theJ-peak. The subsiding blood flow into the aorta from ventricle resultsin the K-Peak. Since most individuals at resting stage, reproduce all ofthe H-I-J-K-L-M-N peaks of a “normal”-looking BCG pattern, thesynchronized H-peak, and the detected I-peak and J-peaks can be used tosequentially find and mark the remaining K-L-M-N peaks. Marking each ofthese peaks enables precise calculation of the H-I slope, the I-J slope,the J-K slope, the K-L slope, the L-M slope, and the M-N slope. Thesedata enable calculations of the time to maximum velocity for each slopethereby enabling calculation of the volumes of blood flow and thepositive and negative pressure values that are exerted on and by thevarious heart muscles and valves. Furthermore, it is also possible toback-calculate from the synchronized H-peak and precisely mark thepreceding g-a¹-a-j-i-h wave patterns.

When individuals with healthy cardiovascular systems, i.e., those withinthe Starr Class 1 range, are stressed such that their heart ratesincrease significantly to supply adequate oxygen in the blood streamthroughout the body, the slopes of their H-I and J-K wave patterns willincrease in height, have steeper slopes and have shorter time period,while the L-M-N waves will repeat distinctly, regularly and their slopesoften become steeper. However, individuals with cardiovascularabnormalities and malfunctions, when stressed, will produce H-I and J-Kslopes that are decreased in height and become longer, i.e., flatter,while L-M-N peaks tend to flatten out as shown in FIGS. 4( b) and 4(c).In cases where the severity of the cardiovascular abnormalities andmalfunctions are increased, the heights of the H, J, L, and N peaks aresignificantly reduced to the point where the H-I, I-J, J-K, K-L, L-M andM-N slopes are similarly elongated and irregular as shown in FIG. 4( c).Table 1 shows a summary of various types of cardiovascular abnormalitiesand their effects on ECG and BCG wave patterns.

TABLE 1 Cardiovascular abnormality ECG Wave Patterns BCG Wave PatternsIschemic Heart hyperacute T wave (tall T wave) increased amplitude in K,J, L, M Diseases (IHD) ST segment Changes. peaks T wave inversion. broadK wave Q wave longer than 0.04 sec. fused H-J wave patterns S in V1 andV2 + R inV5 expiration. R in I + S inIII > 25 mm notched J waves changesin Q-I, Q-J, I-J slopes Sinus Arrhythmia: typical ECG wave patternsprolonged H-I-J wave pattern tachycardia relating to heart rate, P waveor often appears as Starr Class 3 or 4 bradycardia QRS wave patternswave patterns Nonsinus Arrhythmia: ECG shows variable different P-primarily produce Starr Class 3 or ventricular & atrial QRS wavepatterns 4 wave patterns flutter/fibrillation Hypertension variable ECGwave patterns. tall L wave. T inversions large H wave. large S or Rpeaks. H wave fused into the J wave some ECG fluctuations similar tothose for IHD

We have discovered that the H-I-J-K-L-M-N wave peak data collected andcalculated from the synchronized BCG and ECD signals under restingconditions, can be used as reference points to detect and identifydifferent types of potential cardiovascular abnormalities by the changesthat occur in one or more of the H-I, I-J, J-K, K-L, L-M, and M-N slopeswhen the individual is placed under stressed conditions. It is importantto note that regardless of whether an individual is under resting orstressed conditions, synchronization of the H-peak on the BCG with theR-peak on the ECG during resting conditions will enable during stressedconditions, the precise marking of where the H-peak should occur on theBCG from the R-peak on the ECG. It is then possible to mathematicallydetermine where the subsequent I-J-K-L-M-N peaks should have occurred.By referencing the synchronized h-i-j-a-a¹-g-H-I-J-K-L-M-N and wavepeaks and H-I, I-J, J-K, K-L, L-M, M-N slopes produced by the individualunder resting conditions, it is possible to identify and characterizethe changes in the physical movements of the heart muscles and valves,and in the rates and patterns of blood flow into, through and out of theheart under stressed conditions. For example, significant decreases inthe H and J peaks accompanied by elongation of the H-I and J-K slopesunder stress conditions indicate that there is (a) a reduction in therate of increase in intraventricular pressure in response todepolarization of the ventricular muscle pressure, i.e., there is lessventricular contractive force being generated during ventricularsystole, which results in (b) less ejective force exerted on blood flowduring ventricular contraction thereby resulting in a smaller J peak.The reduction in the H and J peaks is primarily as a consequence ofinsufficient oxygen delivery to the heart muscles in the blood returningfrom the lungs to the left atrium to supply the energy required forcontraction of the left ventricle. Prolonged insufficient supply ofoxygenated blood to the left ventricle will result in the decreases inthe H and J peaks becoming more pronounced while the H-I and J-K slopesbecome more elongated. Individuals with severely reduced cardiovascularfunction will have significantly increased heart rates under stress,which can be detected by a significantly reduced time span between theS₁ and S₂ periods, i.e. the time period between the I peak signalingseptum recoil during ventricular contraction and the L peak signallyventricular relaxation during which time the aortic valve is closed bybackflow of blood ejected from the left ventricle. Malfunctioning in theaortic valve, e.g., incomplete closure or leakiness by the aortic valveresults in a greater impact on the left ventricular wall during theearly period of diastole and causes a larger spike, i.e. height in the Npeak. Reduction in the height of the j peak and an elongation of the j-aslope under stressed conditions indicates that the right and left atriaare contracting with less force compared to the resting stage, whiledisappearance of the a¹ peak indicates that the right atrium is notdelivering the same pressurized volume of blood into the right ventriclefor subsequent delivery into the pulmonary artery for transport to thelungs. A reduction or disappearance in the g wave indicates malfunctionor abnormalities in closure of the tricuspid and/or mitral valvesresulting in backflow leakage from the right and left ventricles intothe right and left atria. When an individual with a malfunctioningand/or abnormal cardiosystem is relieved from the stressed conditionsand returns to a resting stage, their ECG and BCG patterns return to thenormal patterns previously recorded before the onset of the stress.

An exemplary embodiment of the present invention for monitoring thephysiological condition of the cardiovascular system and detectingabnormalities is shown in FIG. 5 and generally comprises at least: (1)one device configured for detecting electrical depolarization andre-polarization of an individual's heart tissues and for transmittingsuch information as a ECG signal, (2) one device configured fordetecting physical movements on and/or within the individual's heart andrelated movements on their body surfaces and for transmitting suchinformation as a BCG signal, (3) a device configured for receiving theECG and BCG signals and conditioning at least one of the signals, (4) ananalog-digital converter for converting the signals into digital datathat can be processed and stored, (5) a microprocessor for computing,analyzing, reporting, transmitting and storing the digital data, (6) acomputer software program comprising at least one algorithm configuredfor analyzing the ECG and BCG signals to: (a) detect the P-QRS peaks inan ECG signal, (b) detect and mark the H-I-J peaks in a BCG, (c)synchronize the H peak of the BCG signal with the R peak of the ECGsignal, and (d) provide synchronized ECG and BCG signal outputs, and (7)a graphical user interface (GUI) program written in C++ language.

The system of the present invention may be suitably provided with apulseoximeter configured to concurrently detect at least the amount ofoxygen in the individual's blood and changes in the blood volume intheir skin and transmit these data one of the device configured forreceiving the ECG and BCG data or alternatively, to the microprocessor.The pulseoximeter may be optionally configured to detect and transmitthe individual's heart rate. The system of the present invention maybeoptionally provided with a device configured to detect sounds made bythe heart during its rhythmic systole-diastole periods and to transmit aphonocardiogram signal to the signal conditioning device. The system ofthe present invention may be optionally provided with a deviceconfigured to provide images of the heart during its rhythmicsystole-diastole periods and to transmit an echocardiogram signal to thesignal conditioning device. The computer program may optionally comprisea plurality of cooperating algorithms.

The device configured for receiving the ECG and BCG signals and theanalog-digital converter may comprise a suitably configured motherboardprovided with suitable electronic devices known to those skilled inthese arts. The motherboard may be additionally provided with amicroprocessor configured for receiving and running the software programcomprising one or more mathematical algorithms and/or heuristicalgorithms to at least separately process, analyze and synchronize the Rpeaks and H peaks of the concurrently received ECG and BCG signals andto provide an output comprising at least synchronized ECG-BCGwave-pattern signals. The computer software program may be suitablyprovided with an additional or optionally, a plurality of algorithmsconfigured to heuristically separately process, analyze and synchronizethe concurrently received ECG and BCG signals, and then to heuristicallyidentify and mark the h-i-j-a-a¹-g and I-J-K-L-M-N peaks on thesynchronized BCG signal. The computer software program may be suitablyprovided with at least one addition algorithm or optionally, a pluralityof algorithms configured to process, compare, and analyze pluralities ofsynchronized ECG and BCG signals and to provide outputs relating to thesimilarities and differences among and between the pluralities ofsynchronized ECG and BCG signals.

FIG. 6 shows an exemplary 4-step flowchart according to one embodimentof the present invention, for processing and synchronizing concurrentlyproduced ECG and BCG signals. The first step comprises conditioning ofconcurrently produced ECG and BCG signals to remove extraneous noisecomponents thereby providing signal outputs that are transmitted withminimum relative loss or maximum relative gain. A suitable method forconditioning ECG and BCG signals is to pass each signal separatelythrough fifth-order Butterworth filters wherein: (a) for the ECG signal,the high-pass cutoff frequency is set at about 40 Hz and the low-passfilter is set at about 1 Hz, and (b) for the BCG signal, high-passcutoff frequency is set at about 25 Hz and the low-pass filter is set atabout 1 Hz. The second step is to detect the R wave in the filtered ECGsignal with an algorithm. A suitable algorithm may be developed byexploiting the curve-length concept

which, in reference to FIG. 7, illustrates how the lengths L1 and L2 areable to characterize the shape of the curves, given a certain timeinterval DT. This principle can be applied to detect the wave frontsthat characterize the beginning and the end of an episode arc-lengthrelative to the i-th sample with the chord length, obtaining:

L is the total estimated length of the episode, Tx is the samplinginterval, yi-yi-1 represents the i-th increment and n is a roughestimate of the duration of the episode (or waveform) to be detected: inthis case n is an estimate of QRS duration. L can also be written:

$\begin{matrix}{L = {{{Tx} \cdot {\sum\limits_{i = 0}^{n - 1}\; \sqrt{1 + \frac{( {y_{i} - y_{i - 1}} )^{2}}{{Tx}^{2}}}}} = {{Tx} \cdot {\sum\limits_{i = 0}^{n - 1}\; \sqrt{1 + \frac{{Dy}^{2}}{{Tx}^{2}}}}}}} & (2)\end{matrix}$

Finally, centering the computational window on the i-th sample andcalling w=n/2, a recursive low computational cost form is obtained thatmay be incorporated in to computer software programs using assemblylanguages for DSPs processors known to those skilled in these arts:

The third step is to identify the H peak from the conditioned BCGsignal, then synchronize the H peak with the R peak from the ECG signal,after with the conditioned BCG signal is parsed to locate and mark theh-i-j-a-a¹-g and I-J-K-L-M-N peaks, and then, average the conditionedBCG signal.

Suitable heuristic algorithms for (a) synchronizing the H peak with theR peak then (b) parsing the conditioned BCG signal is parsed to locateand mark the h-i-j-a-a¹-g and I-J-K-L-M-N peaks, and then, (c) averagingthe conditioned BCG signal, may be developed by using the ECG's R peaksas the synchronization points for the cycle-by-cycle lengthdetermination. Each cycle length is than divided into intervalsaccording to the sample rate of the signals. The number of the intervalscan be programmed and experimentally determined. An example is 2500samples equivalent to 1.2 seconds of the acquired signal. The assignedintervals allow the signal processing. The segment points are thanassociated with the ECG pick values, when possible and as the additionalsynchronization option. The segmented signal is used for maxima andminima determination followed by the BCG's letter assignments. Eachsegment can be searched for a local minimum or maximum. The number ofsegments and their programmed assignments permit on a practicaladjustments and experimental set-ups accordingly to the subject groupand analysis requirements.

The assignments generally follow the steps listed below for thesegmented ECG and BCG signals:

-   -   1. first segment in BCG signal after R pick or the segment with        the R pick is searched for a local maximum which determines H        value of the BCG signal,    -   2. next local minimum of BCG signal segments (following H) is        found for the assignment of I value of BCG signal,    -   3. from 1 value the next segments are searched for the local        maximum and J assignment, the next local minimum can be K pick        of BCG signal,    -   4. synchronize and associate the segments and values to the ECG        signal,    -   5. next local maximum of the ECG signal which follows J maximum        (BCH signal) is T pick, the identification of the T permits on        the re-synchronization of the segments,    -   6. the search of the segments following T pick determines the L        (local maximum) and M (the local minimum),    -   7. the next assignment after L and M is the result of the search        of the next local maximum which becomes N pick of the BCG        signal,    -   8. the segmentation permits on the time interval determination        and the back calculation of the time related to the specific        events (pick values),    -   9. the assignments are repeated for each next cycle of BCG        signal as determined by R pick synchronization reference,        after which, the cycle-by-cycle assignments can be averaged or        considered separately.

The fourth step is to producing synchronized and marked outputs of theECG and BCG signals, and transmitting the outputs to at least oneelectronic processing device, one data storage device and one visualoutput device. Exemplary suitable visual output devices include displaymonitors, printers and plotters. The data produced by the individual asdescribed will serve as the resting-stage reference points forsubsequent physiological stress testing outputs, as will be described inmore detail below.

Another embodiment of the present invention comprises detecting,transmitting, conditioning, synchronization, and processing of aplurality of signals produced by an individual's cardiovascular systemduring resting stage conditions, and storing the digital data developedtherefrom in a data storage device. Suitable signals are ECG signals andBCG signals. The signals may optionally or additionally, comprisephonocardiogram and/or echocardiogram signals. While remaining connectedto the system of the present invention, the individual is then placedunder stressed conditions for real-time ongoing detection, transmission,conditioning, synchronization and processing of the signals output bythe individual's cardiovascular system to produce a synchronized ECG-BCGsignal set showing the effects of stress on the signal outputs. Thestressed signal outputs can then be compared using at least onealgorithm, to the resting-stage signal outputs for detection,quantification and assessments of stress-effected variations in thesignal wave patterns and h-i-j-a-a¹-g-H-I-J-K-L-M-N peaks.

After acquisition, processing and extraction of BCG-ECG signal pickvalues and time intervals the comparison of the time-pick values isconducted. The comparison includes the following:

-   -   1. pick values and their respective normalized amplitude values;        the lower or higher values are determined in comparison of the        pre and post exercise assessment,    -   2. the time intervals related to the pick vales are compared and        the differences are derived,        the differences are determined on cycle-by-cycle basis; the        extreme values and the averaged values are recorded and        reported.        The computer software program of the present invention may be        additionally configured to average synchronized outputs for an        individual's resting and stressed stages, and then to overlay        the averaged synchronized outputs to enable visual observation        and analyses of the cardiovascular signal outputs. Since the        data for each signal recording session is storable in a data        storage device, it is possible to collect resting stage signal        data from an individual over an extended period of time, e.g.,        months or years or decades, and then precisely detect and assess        physiological changes that may have occurred in the individual's        resting stage cardiovascular system during these time periods.

The graphical user interface (GUI) of the present invention isconfigured to manage the acquisition, analysis, storage and reporting oflarge sets of ECG-BCG waveforms. A backend data management module may beoptionally provided for efficient interfacing between the GUI and thesynchronized ECG-BCG data stored in a suitable database. An additionalmodule may be provided for computer-aided selection of the individualtailored data-analysis algorithms for analysis and synchronizing ofcertain types of BCG signals, and optionally, computer-selectedcombinations of data-analysis algorithms. It is within the scope of thisinvention that the GUI is suitably configured as shown in FIG. 8:

-   -   (a) to provide at least on module configured receive a plurality        of signals from an individual's cardiovascular system, and        then (i) process, (ii) analyze, (iii) optimize, (iv)        transform, (v) synchronize, and (vi) generate at least one        output comprising at least one synchronized signal wave pattern,    -   (b) with a computer software program configured to provide a        computer-aided process for selection of a suitable data-analysis        algorithm for processing an incoming stream of plurality of        signals from an individual's cardiovascular system, and        optionally, for a selection of a combination of suitable        data-analysis algorithms, and    -   (c) to provide a data flow management module for communicating        and cooperating with a data storage device, and    -   (d) to provide an outputs management module for communicating        synchronized ECG-BCG signal outputs to devices exemplified by        monitors, screens, printers and plotters.

Referring to FIG. 8, the GUI is in windows GUI format through MicrosoftFoundation Class (MFC). It provides the basic system layout, waveformdisplay, as well as various buttons, inputs, and fields associated withdata management and analysis function calls FIG. 9. The GUI provides theuser access to retrieve and analyze the waveforms from the database. Amodel GUI drawing is attached in the appendix to provide more detail tothe basic design of the GUI. The database management module is a libraryof general functions providing the User Interface Module access to thedatabase. Basic functions may include, “read”, “write to datatable”,“add subfolder”, “retrieve wavefile”, and “save/resave wavefile”. Thewaveform display module suitably comprises a library of generalfunctions. It may additionally contain basic waveform display functionssuch as “draw and erase waveforms”, “scrolling display and zooming”,“select points on waveform”, select cycles on waveform”, and “get valueson wavepoints”. The waveform analysis module suitable comprises alibrary collection of functions. These functions are linkable functionsthat the User Interface Module can call upon to provide outputs to thewaveform analysis module. The basic function groups will includealgorithms to “detect wave slopes”, “amplitude”, “interwavelet delavs”,“cycle detection”, “averaging” and other analysis algorithms known tothose skilled in these arts to be useful for analyzing ECG or BCGsignals.

FIG. 10 shows an exemplary basic layout for a database structure usefulto storing sets of ECG-BCG waveforms provided by the present invention.The database is contained inside a main folder, the database folder.This database folder contains a SQL (similar to Access) type data table.The SQL data table stores information for each subject and references tothe waveforms associated (FIG. 11). The waveform data files for eachsubject are stored under subfolders located under the same main folder.There may be several waveform data files during a single session for thesame subject, thus an exemplary naming convention has been establishedto maintain reliable referencing. The exemplary file naming conventionis as follows: first, a 4-digit subject ID is placed, followed by anunderscore, then the location of the BCG reading is indicated byappending either PMI (4/5-intercostal) or STR (sternal), followed byanother underscore, then pre- or post-exercise reading is indicated byappending PRE (for pre-exercise) or POS (for post-exercise), followed bythe number of the recording, followed by another underscore, thenfinally the date is appended using the year-month-date convention(YYYYMMDD). The template for the filename would read the as follows:

XXXX_PMI/STR_PRE/POS#_YYYYMMDD

An exemplary method for the use of the system of the present inventionfor monitoring the physiological condition of an individual'scardiovascular systems and for early identification cardiovascularabnormalities and malfunctions is provided below. Referring again toFIG. 5, the first step is to collect and input into the GUI, theindividual's: (a) medical history relating to their cardiovascularsystem, (b) lifestyle characteristics such smoking, drinking, nutrition,drug use habits and other lifestyle habits, (c) physical activity level;and (d) physical and genetic information including race, weight, height,circumference of their body around the hips, circumference of their bodyaround the waist, age, and sex. The second step is to measure theirblood pressure with a suitable blood pressure measuring deviceexemplified by CAS Vital Signs Monitors Models 740, 750C and 750 E (CASMedical Systems Inc., Branford, Conn., USA). It is suitable for theindividual to remain interconnected with the blood pressure measuringdevice for the duration of the testing period. The third step is toattach an appropriate number of electrocardiograph (ECG) electrodes toappropriate sites on the individual's body and then connect the ECGelectrodes to a suitable ECG system. The fourth step is for theindividual to lie in a prone position after which, a suitableballistocardiograph (BCG) accelerometer as exemplified by those suppliedby Brüel & Kjær (Skodsborgvej 307, DK-2850, Nærum, Denmark) is attachedto the base of the individual's sternum with hypoallergenic double-sidedadhesive tape, It is also suitable to clip a pulseoximeter to theindividual's finger. Exemplary suitable pulseoximeters include Nonin8600 pulseoximeters (Nonin Medical Inc., Plymouth, MM, USA) and CASVital Signs Monitors Models 740, 750C and 750 E (CAS Medical SystemsInc.). The sixth step is to record the individual's resting-stage ECG,BCG, blood pressure, heart rate and blood oxygen concentration signaldata for a selected period of time while they are lying in a proneposition and breathing normally. An exemplary suitable resting-stagedata collection period is about three minutes, but this data collectionperiod may be adjusted as determined to be appropriate by the medicalpersonnel conducting the testing of the individual. It is preferablethat a plurality of BCG data collections is conducted during theresting-stage data collection period. A suitable number of BCG datacollections during this period is three. The seventh step is for theindividual to perform a selected physical exercise for a selectedsuitable period of time appropriate for the selected physical exercise.Exemplary suitable physical exercises include pedaling on a stationarybicycle, running or walking on a treadmill, manipulating a StairMaster®exercise device (StairMaster is a registered trademark of StairMasterSports/Medical Products, Inc., Vancouver Wash., USA), jogging, swimmingand the like. The eighth step is for the individual to lie down into aprone position immediately after the period of physical exercise hasended for recording of the individual's post-exercise ECG, BCG, bloodpressure, heart rate and blood oxygen concentration signal data for aselected period of time. An exemplary suitable post-exercise datacollection period is about three minutes, but this data collectionperiod may be adjusted as determined to be appropriate by the medicalpersonnel conducting the testing of the individual. It is preferablethat a plurality of BCG data collections is conducted during theresting-stage data collection period. A suitable number of BCG datacollections during this period is three.

The subject information, resting-stage, and post-exercise data inputsare transmitted to the database engine where they are stored in separatefiles in the database, and are accessible for processing,synchronization, and analyses by the algorithms of the present inventiondisclosed herein for synchronization of the R peak of the ECG signal andthe H peak of the BCG signal for each set of ECG and BCG signalsconcurrently collected from the individual during their rest-stage andpost-exercise periods. The processed data is stored in separate files inthe database, and are displayable on suitable monitors and screens, andprintable by suitable printers and plotters. Comparisons of theindividual's resting-stage and post-exercise synchronized ECG-BCG wavepatterns generated by the algorithms of the present inventions willenable detection and assessments in stress-induced changes in theindividual's BCG wave patterns and related h-i j-a-a¹-g-H-I-J-K-L-M-Npeaks.

In accordance with one exemplary embodiment, the system may be used as aroutine testing method in a clinical environment as exemplified by aMedical Doctor's office, a walk-in clinic, a clinical laboratory, atesting facility associated with a medical research institute, a testingfacility associated with a hospital, and the like.

In accordance with another exemplary embodiment, the system may beoptionally adapted for employment in exercise and training facilitiesfor observing, recording and storing changes in an individual'scardiovascular system during periods of exercise and training for thepurposes of monitoring improvements in cardiovascular fitness and fordetection of onset of potential cardiovascular malfunctions.

In accordance with another exemplary embodiment, resting-stagecardiovascular data and related synchronized ECG-BCG wave patterns maybe collected from a plurality of individuals, compiled and stored in adatabase file for use as a “population” sized reference point forcomparing individuals' resting-stage synchronized ECG-BCG wave patterns.It is within the scope of the present invention to separate and grouppluralities of resting-stage synchronized ECG-BCG wave patterns inaccordance to, for example, the Starr classification system to provide“population” sized reference groups of healthy individuals with idealsynchronized ECG-BCG wave patterns (i.e., resting-stage Class 1),individuals with somewhat less than ideal synchronized ECG-BCG wavepatterns (i.e., resting-stage Class 2), individuals whose synchronizedECG-BCG wave patterns show debilitation of cardiovascular function underresting conditions (i.e., resting-stage Class 3), and individuals whosesynchronized ECG-BCG wave patterns show significant debilitation ofcardiovascular function under resting conditions (i.e., resting-stageClass 4).

The system and methods of the present invention for monitoringcardiovascular physiological conditions and for detecting relatedabnormalities and malfunctions are described in more detail in thefollowing examples.

EXAMPLE 1

An exemplary system of the present invention was configured as shown inFig. comprising the following components:

-   -   1. CSA 750C Multi-Parameter Monitor (CAS Medical Systems Inc.)        for monitoring blood pressure, heart rate and blood oxygen        levels.    -   2. Burdick® EK10 12 lead, single channel electrocardiograph        (Cardiac Science Corp., Bothell, Wash., USA) for detection and        transmission of ECG signals.    -   3. Brüel & Kjær® (Brüel & Kjæer is a registered trademark of        Brüel & Kjær Sound & Vibration; Measurement A/S, Nærum, Denmark)        Type 4381 accelerometer coupled with a Brüel & Kjær® Type 2635        charge amplifier for detection and transmission of BCG signals.    -   4. LabVIEW® (LabVIEW is a registered trademark of National        Instruments Corp., Austin, Tex., USA) 8.2 data acquisition        system installed on an IBM laptop computer, for concurrently        receiving ECG and BCG signals from the ECG and BCG instruments    -   5. A software program comprising the algorithms described herein        for conditioning and synchronizing ECG and BCG, and configured        to communicate with the LabVIEW® 8.2 data acquisition system.    -   6. A database program configured to receive, store and display        conditioned raw and synchronized ECG and BCG signal sets.    -   7. A stationary exercise cycle.

The system was used to collect, condition, synchronize, process,analyze, store and report resting-stage and post-exercise cardiovasculardata from 142 individuals. Each individual was assessed for a period of30 minutes as follows: First, their medical history was filled in on aquestionnaire comprising the following questions:

-   -   (1) medical history of their heart (including all know heart        conditions),    -   (2) lifestyle habits (i.e. smoking drinking, drug use, stress        levels, etc.),    -   (3) physical activity level,    -   (4) race,    -   (5) weight,    -   (6) height,    -   (7) hip circumference,    -   (8) waist circumference,    -   (9) body fat %,    -   (10) age, and    -   (11) sex.

Next, the individual's blood pressure was recorded after which, ECGelectrodes to both of their shoulders and just above both hips, afterwhich the electrodes were attached to the Burdick® EK10electrocardiograph. Then, the Brüel & Kjær® Type 4381 accelerometer andType 2635 charge amplifier were attached with hypoallergenicdouble-sided adhesive tape to the base of the individual's sternum.Then, the pulseoximeter provided with the CSA 750C Multi-ParameterMonitor was clipped onto one of the individual's forefingers andconnected to the Monitor. The individual then lay very still in a proneposition on a padded board while breathing normally while three1-minute-long BCG recordings were collected, with 1-minute rest periodsbetween each 1-minute recording period. The pulseoximeter,ballistocardiography, ECG, and blood pressure equipment weredisconnected from the individual who was then asked to pedal thestationary exercise cycle for a 1-minute period or alternatively,depending on the physical condition of the individual, walk around a setcourse for 1 minute. They were then asked to again to lie down verystill in a prone position on the padded board while the equipment wasreconnected to the individual for collection of post-exercise bloodpressure, heart rate, blood oxygen concentration, ECG signals plus three1-minute BCG recordings, with 1-minute rests periods between each1-minute recording period.

The resting-stage and post-exercise ECG and BCG signals were conditionedby (a) passing the ECG signals through a fifth-order Butterworth filterwith the high-pass cutoff frequency set at about 40 HZ and the low-passfilter set at about 1 Hz, and (b) passing the BCG signals through afifth-order Butterworth filter with the high-pass cutoff frequency setat about 25 Hz and the low-pass frequency set at about 1 Hz. Thealgorithms described herein were applied to each ECG-BCG signal sets to(a) identify the R peaks, (b) synchronize the H peaks with the R peaks,(b) parsing the conditioned BCG signals to locate and mark theh-i-j-a-a¹-g and I-J-K-L-M-N peaks, and then, (c) averaging theconditioned resting-stage and post-exercise BCG signals.

EXAMPLE 2

FIG. 12 a shows the raw, unconditioned ECG and BCG signals produced by ahealthy individual with a normally function cardiovascular system,during a pre-exercise non-stressed resting-stage period. Additionalcardiophysiological data collected as described in Example 1, werestored in the system's database. FIG. 12 b shows the raw, unconditionedECG and BCG signals produced by the same individual after a period ofphysical exercise administered as outlined in Example 1. The R-peaks ofthe ECG signal during the pre-exercise resting stage (FIG. 12 a) wereused by the heuristic algorithms to mark and synchronize the BCG H-peakswith said concurrently collected ECG R-peaks. The heuristic algorithmssubsequently marked and correlated the subsequent I-J-K-L-M-N peaks andproduced the synchronized ECG-BCG cycle patterns shown in FIG. 13 a. Ina similar way, the R-peaks of the ECG signal during the post-exercisestage (FIG. 12 b) were used by the heuristic algorithms to mark andsynchronize algorithms subsequently marked and correlated the subsequentI-J-K-L-M-N peaks and produced the synchronized ECG-BCG cycle patternsshown in FIG. 13 b. Finally, the software program compared and assessedsynchronized BCG patterns to determined if significant changes occurredin the physical functioning of the various heart components asexemplified by the vigor of cardiac ejection of blood from the atria andventricles, and the speed of filling of the atrial chambers during thediastolic period, and the related physical movements of the heartmuscles, valves, and related flows of blood into, between and out of theatria and ventricles. FIG. 13 c shows a comparison of the pre-exerciseand post-exercise synchronized BCG signals produced by the exemplarysystem of the present during one cycle, i.e. heart beat. In this healthyindividual, the pre- and post-exercise BCG patterns are identicalshowing that the electrical, physical and physiological components ofthe heart were not affected by the application of stress.

EXAMPLE 3

FIGS. 14 a and 14 b show the raw, unconditioned ECG and BCG signalsproduced by an individual before and after stress induced by physicalexercise as described in Example 1. This individual had previouslyexperience and recovered from a mild heart attack, and is in the processof modifying their lifestyle in order to strengthen their cardiovascularsystem. This individual's post-exercise heart rate was about 65%-70% (5beats in a 3-second interval) greater than the pre-exercise rate (3beats in a 3-second interval) (FIGS. 14 a and 14 b). More significant,however, are the changes that are evident after the signal conditioningto remove the background noise and synchronization of the BCG signalswith the ECG signals (FIGS. 15 a and 15 b), that show the increasedheart rates is accompanied by increased physical intensities in themovements of the heart muscles and valves (FIG. 15 b). However,comparison of the pre- and post-exercise synchronized BCG signals showthat the H-I-J-K-L-K-M-N peaks in the pre-exercise BCG signal pattern,the peaks between the H-I-J-K-L-K-M-N are flattened out and that thedemarcation between the peaks is significantly diminished (FIG. 15 a).However, their post-exercise synchronized BCG signal (FIG. 15 b) showsthat a clearly distinguishable H-I-J-K pattern was temporarilyreestablished, presumably for a brief period of time to supply anincreased supply of oxygen to the heart muscles. However, the presenceof this “normal-appearing” BCG pattern during the post-exercise periodsuggests that this individual has the potential to restore hiscardiovascular system to approximate the functioning of the individualtested in Example 2. So, although in this example, the individual's rawunconditioned pre- and post-exercise ECG and BCG signals appeared to benormal although with an elevated heart rate, the system and the softwareof the present invention provided the means for detecting physiologicalabnormalities associated with physical malfunctioning with one or moreof their heart valves, heart muscles and vascular system. Furthermore,it is within the scope of this invention to store such data produced byan individual during sampling periods over extended periods of time, sothat improvements in the individual's cardiovascular system's functionand capacity can be recorded and reported as part of treatment, therapy,exercise programs and the like.

EXAMPLE 4

FIGS. 16 a and 16 b show the raw, unconditioned ECG and BCG signalsproduced by an individual before and after stress induced by physicalexercise as described in Example 1. This individual is consideredat-risk based on the sporadic breakdown in their post-exercise ECGsignal (FIG. 16 b) in conjunction with the substantial decreases in theamplitudes of the BCG signals (FIG. 16 b). However, conditioning the ECGand BCG signals and synchronizing the BCG signal with the ECG signalshowed that, during the pre-exercise resting period, the magnitude ofthe BCG H-I-J-K-L-K-M-N peaks are even more diminished than was seenwith the unhealthy individual in Example 3 with only the H-I waveclearly identifiable (FIGS. 17 a and 17 c). Although the intensity ofthe BCG peaks increased post-stress (FIG. 17 b), the amplitudes of thepeaks within the wave pattern were approximately the same suggestingthat even under stress, the post-right-ventricular contraction movementsof the heart produce as much signal amplitude as do the septum recoil(i.e., the H-I wave) and flow of blood into the pulmonary and aorticarteries (i.e., J-K wave). In a healthy individual as exemplified inExample 2 (FIG. 13 b), the amplitudes of the H-I and J-K waves aretypically greater than subsequent L-M-N waves.

EXAMPLE 5

FIGS. 18 a, 18 b, and 18 c compare the conditioned synchronized pre- andpost exercise BCG signals from a healthy individual (FIG. 15 a is takenfrom FIG. 13 c), an unhealthy individual (FIG. 15 b is taken from FIG.15 c) and an at-risk individual (FIG. 15 c is taken from FIG. 17 c). Aspreviously discussed, the healthy individual's pre- and post-exercisesynchronized BCG wave patterns are identical (FIG. 18 a). The unhealthyindividual's pre-exercise BCG wave pattern (FIG. 18 b) has substantiallydiminished H, J, and L peaks accompanied by flattened and elongated H-Iand J-K waves (exemplified by H¹, I¹, J¹ and K¹) while after exercise,the amplitudes of the H, J, and L peaks increase considerably, the H-Iand J-K waves are more clearly defined, and the L-M-N waves appear(exemplified by H², I², J², K², L², M², N²). The at-risk individual'spre-exercise BCG wave pattern exemplified by H¹, I¹, J¹ and K¹ peaks(FIG. 18 c) is similar to the unhealthy individual's pre-exercise BCGwave (FIG. 18 b). However, the at-risk individual's post-exercise BCGwave pattern exemplified by H², I², J², K², L², M², N² peaks (FIG. 18 c)is different from the unhealthy individual's BCG wave pattern (FIG. 18b) indicating that different components of the at-risk individual'scardiovascular system are abnormal relative to the unhealthyindividual's system, both systems in comparison to the healthyindividual's system as exemplified by the post-exercise BCG wave patternin FIG. 18 a. Those skilled in these arts will understand that storingsuch data in a database for future reference to in comparison with latercollected ECG and BCG data with the exemplary systems of the presentinvention, will enable: (1) assessments of the improvements ordeterioration in an individual's cardiovascular system over a period oftime, and also, (2) comparisons of the responses of an individual'scardiovascular systems pre- and post-stress to a broad populationdatabase.

While this invention has been described with respect to the exemplaryembodiments, those skilled in these arts will understand how to modifyand adapt the systems, methods, algorithms and heuristic methodsdisclosed herein for monitoring the physiological condition ofcardiovascular systems and for detecting abnormalities and malfunctionstherein by conditioning and synchronizing exemplary ECG and BCG signalsfor other applications. For example, the system of the present inventionmay be additionally provided with an implantable device configured forinstallation within an individual's body and for receiving thereinelectrical signals derived from the conditioned and synchronized ECG-BCGsignal sets, and for transmitting the derived electrical signals to atarget site within the individual's body for affecting a physiologicalresponse therein. Furthermore, it is possible for those skilled in thesearts to adapt the systems, methods and algorithms disclosed herein formonitoring the physiological condition of other types of mammaliansystems wherein a plurality of detectable signals are generated wherebythe signals are acquired, processed, synchronized and retransmitted forstorage and/or reporting and/or for providing returning stimulatorysignals to the originating mammalian systems. Examples of suchmodifications include providing alternative types of paired signals forcondition and synchronization as exemplified by signals quantifyinglevels of blood sugar paired with signals for example quantifying bloodoxygen levels or alternatively, insulin levels, or alternatively,electrical impulses transmitted by the peripheral nervous system pairedwith electrical impulses transmitted by the central nervous systems, orfurther alternatively, with signals generated by systemic antibodies tovarious and individual types of cancers paired with signals generated byselected systemic biochemical markers such as proteins, and the like.Therefore, it is to be understood that various alterations andmodifications can be made to the systems, methods and algorithmsdisclosed herein for monitoring the physiological condition anddetecting abnormalities therein, within the scope of this invention.

What is claimed is:
 1. A system for monitoring an individual'sphysiological condition and detecting abnormalities therein, the systemcomprising; a first device comprising a device configured for at leastreceiving, displaying and transmitting a first plurality of signalscomprising electrical signals; a set of electrodes wherein eachelectrode is capable of detecting electrical activity associated with aphysiological condition of the individual and producing a correspondingelectrical signal, said set of electrodes configured for attachment tothe individual's body and for communicating with and cooperating withsaid first device; a second device configured for receiving andtransmitting a second plurality of signals from the individual's body,said second plurality of signals selected from the group comprisingseismic signals, acoustic signals, image signals, chemical signals,biochemical signals and electrical signals; a third device capable ofreceiving therein the first plurality and the second plurality ofsignals, said third device configured for conditioning the firstplurality of signals and the second plurality of signals, and fortransmitting said conditioned first plurality of signals and saidconditioned second plurality of signals; a software program providedwith at least one algorithm configured for processing and synchronizingsaid conditioned first plurality of signals and said conditioned secondplurality of signals, and deriving an output from said synchronizedsignals; a microprocessor capable of receiving said conditioned firstplurality of signals and said conditioned second plurality of signalsfrom the third device, said microprocessor configured to cooperate withthe software program to process and synchronize said conditioned firstplurality of signals and said conditioned second plurality of signals,and to generate an output derived therefrom said synchronized signalsindicative of the individual's physiological condition; and a databaseprovided for storing therein signals transmitted from the first, secondand third devices, and outputs generated by the microprocessor.
 2. Asystem according to claim 1, wherein the first device comprises anelectrocardiograph configured for at least receiving, displaying andtransmitting a first plurality of signals comprising ECG signals, andthe set of electrodes comprises a plurality of electrodes capable ofdetecting electrical activity associated with the heart beat of anindividual and producing corresponding ECG signals, said set ofelectrodes configured for attachment to the individual's body and forcommunicating with and cooperating with said electrocardiograph.
 3. Asystem according to claim 2, wherein the second device is selected fromthe group comprising ballistocardiographs and seismocardiographs, and isconfigured for at least receiving, displaying and transmitting a secondplurality of signals comprising BCG signals produced in and on theindividual's body as a result of cardiovascular system function, saidsecond device provided with at least one seismic sensor configured forcommunicating with the individual's body.
 4. A system according to claim3, wherein the seismic sensor is an accelerometer.
 5. A system accordingto claim 4, wherein the accelerometer is coupled to a charge amplifier.6. A system according to claim 2, additionally provided with at leastone device configured for measuring at least one physiological parameterselected from the group comprising blood pressure, heart rate, and bloodoxygen concentration.
 7. A system according to claim 2, additionallyprovided with a graphical user interface configured to enable anoperator to input data into the database, and to access signals andoutputs stored therein the database.
 8. A system according to claim 2,wherein the first plurality of signals is conditioned by passing saidsignals through a filter provided with a high-pass cutoff frequency ofabout 40 Hz and a low-pass filter of about 1 Hz.
 9. A system accordingto claim 3, wherein the second plurality of signals is conditioned bypassing said signals through a filter provided with a high-pass cutofffrequency of about 25 Hz and a low-pass filter of about 1 Hz.
 10. Asystem according to claim 3, wherein the software program is providedwith a at least one algorithm configured to firstly, detect and mark afirst reference peak in a repeating cycle of wave patterns comprisingthe conditioned first plurality of ECG signals, then secondly, detectand mark a selected second reference peak in a repeating cycle of wavepatterns comprising the conditioned second plurality of BCG signals,then thirdly, synchronize the first reference peak and the secondreference peak thereby synchronizing the conditioned first plurality ofECG signals and the conditioned second plurality of BCG signals andproducing a synchronized paired ECG-BCG signal set therefrom.
 11. Asystem according to claim 10, wherein the first reference peak is a Rpeak in the first plurality of ECG signals, and the second referencepeak is a H peak in the second plurality of BCG signals.
 12. A systemaccording to claim 3, wherein the software program is provided with aplurality of algorithms, wherein: a first algorithm is configured tofirstly, detect and mark a first reference peak in a repeating cycle ofwave patterns comprising the conditioned first plurality of ECG signals,then secondly, detect and mark a selected second reference peak in arepeating cycle of wave patterns comprising the conditioned secondplurality of BCG signals, then thirdly, synchronize the first referencepeak and the second reference peak thereby synchronizing the conditionedfirst plurality of ECG signals and the conditioned second plurality ofBCG signals and producing a synchronized paired ECG-BCG signal settherefrom; and a second algorithm is configured for analyzing thesynchronized paired ECG-BCG signal set, deriving, identifying, marking,and characterizing therefrom: (a) the individual wave componentscomprising the repeating cycles of the conditioned first plurality ofECG signals, and (b) the individual wave components comprising therepeating cycles of the conditioned second plurality of BCG signals, andproducing an output therefrom.
 13. A system according to claim 12,wherein the first reference peak is a R peak in the first plurality ofECG signals, and the second reference peak is a H peak in the secondplurality of BCG signals.
 14. A system according to claim 12, whereinthe individual wave components comprising the repeating cycles of theconditioned first plurality of ECG signals comprise P-Q-R-S-T peaks, andthe individual wave components comprising the repeating cycles of theconditioned second plurality of BCG signals comprise at least H-I-J-K-Lpeaks.
 15. A system according to claim 3, wherein the software programis provided with a plurality of algorithms, wherein: a first algorithmis configured to firstly, detect and mark a first reference peak in arepeating cycle of wave patterns comprising the conditioned firstplurality of ECG signals, then secondly, detect and mark a selectedsecond reference peak in a repeating cycle of wave patterns comprisingthe conditioned second plurality of BCG signals, then thirdly,synchronize the first reference peak and the second reference peakthereby synchronizing the conditioned first plurality of ECG signals andthe conditioned second plurality of BCG signals and producing asynchronized paired ECG-BCG signal set therefrom; a second algorithm isconfigured for analyzing the synchronized paired ECG-BCG signal set,deriving, identifying, marking, and characterizing therefrom: (a) theindividual wave components comprising the repeating cycles of theconditioned first plurality of ECG signals, and (b) the individual wavecomponents comprising the repeating cycles of the conditioned secondplurality of BCG signals, and producing an output therefrom; and a thirdalgorithm is configured for comparing the individual wave componentscomprising the repeating cycles of the conditioned first plurality ofECG signals and the conditioned second plurality of BCG signals producedby the second algorithm, with the individual wave components comprisingthe repeating cycles of the conditioned first plurality of ECG signalsand the conditioned second plurality of BCG signals of at least oneselected synchronized paired ECG-BCG signal set stored in the database,and to produce an output therefrom, said output storable in thedatabase.
 16. A system according to claim 12, wherein the at least oneselected synchronized paired ECG-BCG signal set stored in the databaseis the individual's resting-stage ECG-BCG signal set, and thesynchronized paired ECG-BCG signal set produced by the second algorithmis the individual's post-exercise ECG-BCG signal set
 17. A systemaccording to claim 3, wherein the software program is provided with aplurality of algorithms, wherein: a first algorithm is configured tofirstly, detect and mark a first reference peak in a repeating cycle ofwave patterns comprising the conditioned first plurality of ECG signals,then secondly, detect and mark a selected second reference peak in arepeating cycle of wave patterns comprising the conditioned secondplurality of BCG signals, then thirdly, synchronize the first referencepeak and the second reference peak thereby synchronizing the conditionedfirst plurality of ECG signals and the conditioned second plurality ofBCG signals and producing a synchronized paired ECG-BCG signal settherefrom; a second algorithm is configured for analyzing thesynchronized paired ECG-BCG signal set, deriving, identifying, marking,and characterizing therefrom: (a) the individual wave componentscomprising the repeating cycles of the conditioned first plurality ofECG signals, and (b) the individual wave components comprising therepeating cycles of the conditioned second plurality of BCG signals, andproducing an output therefrom; and a third algorithm is configured forcomparing the individual wave components comprising the repeating cyclesof the conditioned first plurality of ECG signals and the conditionedsecond plurality of BCG signals produced by the second algorithm, withthe individual wave components comprising the repeating cycles of theconditioned first plurality of ECG signals and the conditioned secondplurality of BCG signals of a selected plurality of synchronized pairedECG-BCG signal sets stored in the database, and to produce an outputtherefrom, said output storable in the database.
 18. A system accordingto claim 14, wherein the synchronized paired ECG-BCG signal set producedby the second algorithm is the individual's resting-stage ECG-BCG signalset, and the selected plurality of synchronized paired ECG-BCG signalsets comprises stored in the database comprises a plurality ofsynchronized resting-stage paired ECG-BCG signal sets produced from theindividual during a plurality of spaced apart testing periods.
 19. Asystem according to claim 14, wherein the synchronized paired ECG-BCGsignal set produced by the second algorithm is the individual'sresting-stage ECG-BCG signal set, and the selected plurality ofsynchronized paired ECG-BCG signal sets comprises stored in the databasecomprises synchronized resting-stage paired ECG-BCG signal sets producedfrom a plurality of individuals.
 20. As system according to claim 3,additionally provided with a fourth device configured to receive thereinthe outputs generated from said synchronized signals and to derive andproduce therefrom electrical signals, said fourth device capable ofcontrollably transmitting said electrical signals; and a fifth devicecapable of receiving from the fourth device said electrical signals,said fifth device configured for controllably
 21. A method, using thesystem of claim 1, for monitoring an individual's physiologicalcondition and detecting abnormalities therein, the method comprising;attaching the set of electrodes to selected points on the individual'sbody and interconnecting said electrodes with the first device;additionally attaching to a selected point on the individual's body atleast one appropriate signal detection device configured forcommunication with the second device and interconnecting said signaldetection device with the second device; interconnecting the first andsecond devices with the third device, the microprocessor provided withthe software program, and with the database; recording, processing andstoring at least one set of resting-stage data for a selected period oftime while the individual is lying in a prone position; disconnectingthe first and second devices from the set of electrodes and signaldetection device, and the subjecting the individual to a selected stressfor a selected period of time; reconnecting the first and second devicesto the set of electrodes and signal detection device, and thenrecording, processing and storing at least one set of post-stress datafor a selected period of time while the individual is lying in a proneposition; comparing the at least one set of post-stress data to the atleast one set of resting-stage data.
 22. A method according to claim 21,wherein the first device comprises an electrocardiograph configured forat least receiving, displaying and transmitting a plurality of signalscomprising ECG signals, and the set of electrodes comprises a pluralityof electrodes capable of detecting electrical activity associated withthe heart beat of an individual and producing corresponding ECG signals.23. A method according to claim 22, wherein the second device isselected from the group comprising ballistocardiographs andseismocardiographs, and is configured for at least receiving from anappropriate signal detection device, displaying and transmitting aplurality of signals comprising BCG signals produced in and on theindividual's body as a result of cardiovascular system function, saidsecond device provided with at least one seismic sensor configured forcommunicating with the individual's body.
 24. A method according toclaim 23, wherein the signal detection device is an accelerometer.
 25. Amethod according to claim 24, wherein the accelerometer is coupled to acharge amplifier.
 26. A method according to claim 23, wherein the systemis additionally provided with at least one device configured formeasuring at least one physiological parameter selected from the groupcomprising blood pressure, heart rate, and blood oxygen concentration.27. A method according to claim 23, wherein a graphical user interfaceis provided to enable an operator to input data into the database, andto access signals and outputs stored therein the database.
 28. A methodaccording to claim 23 wherein the resting-stage
 29. A method accordingto claim 23, wherein the first plurality of ECG signals is conditionedby passing said signals through a filter provided with a high-passcutoff frequency of about 40 Hz and a low-pass filter of about 1 Hz. 30.A method according to claim 23, wherein the second plurality of BCGsignals is conditioned by passing said signals through a filter providedwith a high-pass cutoff frequency of about 25 Hz and a low-pass filterof about 1 Hz.
 31. A method according to claim 23, wherein: (a) theresting-stage data comprise a first plurality of conditioned ECG signalsand a second plurality of conditioned BCG signals, and (b) thepost-exercise data comprise a first plurality of conditioned ECG signalsand a second plurality of conditioned BCG signals.
 32. A methodaccording to claim 31, wherein the resting-stage data and thepost-exercise data are separately processed, analyzed and characterizedby a software program provided with at least one algorithm configuredto: firstly, detect and mark a first reference peak in a repeating cycleof wave patterns comprising the conditioned first plurality of ECGsignals, then secondly, detect and mark a selected second reference peakin a repeating cycle of wave patterns comprising the conditioned secondplurality of BCG signals, then thirdly, synchronize the first referencepeak and the second reference peak thereby synchronizing the conditionedfirst plurality of ECG signals and the conditioned second plurality ofBCG signals and producing a synchronized paired ECG-BCG signal settherefrom; thereby producing a first synchronized paired ECG-BCG signalset therefrom the resting-stage data, and a second synchronized pairedECG-BCG signal set therefrom post-exercise data.
 33. A method accordingto claim 32, wherein the first reference peak is a R peak in the firstplurality of ECG signals, and the second reference peak is a H peak inthe second plurality of BCG signals.
 34. A method according to claim 31,wherein the resting-stage data and the post-exercise data are separatelyprocessed, analyzed and characterized by a software program providedwith a plurality of algorithms, wherein: the first algorithm isconfigured to firstly, detect and mark a first reference peak in arepeating cycle of wave patterns comprising the conditioned firstplurality of ECG signals, then secondly, detect and mark a selectedsecond reference peak in a repeating cycle of wave patterns comprisingthe conditioned second plurality of BCG signals, then thirdly,synchronize the first reference peak and the second reference peakthereby synchronizing the conditioned first plurality of ECG signals andthe conditioned second plurality of BCG signals and producing asynchronized paired ECG-BCG signal set therefrom, thereby producing afirst synchronized paired ECG-BCG signal set therefrom the resting-stagedata, and a second synchronized paired ECG-BCG signal set therefrompost-exercise data; and the second algorithm is configured for analyzingthe synchronized paired ECG-BCG signal sets, deriving, identifying,marking, and characterizing therefrom: (a) the individual wavecomponents comprising the repeating cycles of the conditioned firstplurality of ECG signals, and (b) the individual wave componentscomprising the repeating cycles of the conditioned second plurality ofBCG signals, thereby producing first output from the resting-stagesynchronized paired ECG-BCG signal set, and a second output from thepost-exercise synchronized paired ECG-BCG signal set.
 35. A methodaccording to claim 34, wherein the first reference peak is a R peak inthe first plurality of ECG signals, and the second reference peak is a Hpeak in the second plurality of BCG signals.
 36. A method according toclaim 34, wherein the individual wave components comprise the repeatingcycles of the conditioned first plurality of ECG signals compriseP-Q-R-S-T peaks, and the individual wave components comprise therepeating cycles of the conditioned second plurality of BCG signalscomprise at least H-I-J-K-L peaks.
 37. A method according to claim 31,wherein the resting-stage data and the post-exercise data are separatelyprocessed, analyzed and characterized by a software program providedwith a plurality of algorithms, wherein: a first algorithm is configuredto firstly, detect and mark a first reference peak in a repeating cycleof wave patterns comprising the conditioned first plurality of ECGsignals, then secondly, detect and mark a selected second reference peakin a repeating cycle of wave patterns comprising the conditioned secondplurality of BCG signals, then thirdly, synchronize the first referencepeak and the second reference peak thereby synchronizing the conditionedfirst plurality of ECG signals and the conditioned second plurality ofBCG signals and producing a synchronized paired ECG-BCG signal settherefrom, thereby producing a first synchronized paired ECG-BCG signalset therefrom the resting-stage data, and a second synchronized pairedECG-BCG signal set therefrom post-exercise data; a second algorithm isconfigured for analyzing the synchronized paired ECG-BCG signal sets,deriving, identifying, marking, and characterizing therefrom: (a) theindividual wave components comprising the repeating cycles of theconditioned first plurality of ECG signals, and (b) the individual wavecomponents comprising the repeating cycles of the conditioned secondplurality of BCG signals, thereby producing first output from theresting-stage synchronized paired ECG-BCG signal set, and a secondoutput from the post-exercise synchronized paired ECG-BCG signal set;and a third algorithm is configured for comparing the individual wavecomponents comprising the repeating cycles of the conditionedresting-stage synchronized paired ECG-BCG signal set, with theindividual wave components comprising the repeating cycles of theconditioned post-exercise synchronized paired ECG-BCG signal, and toproduce an output therefrom, said output storable in the database.
 38. Amethod according to claim 37, wherein the third algorithm isadditionally configured for comparing the individual wave componentscomprising the repeating cycles of one of the conditioned resting-stagesynchronized paired ECG-BCG signal set and the conditioned post-exercisesynchronized paired ECG-BCG signal, with a plurality of synchronizedpaired ECG-BCG signals selected from the database, and to produceoutputs therefrom,
 39. A method according to claim 38, wherein theplurality of synchronized paired ECG-BCG signals selected from thedatabase comprise a plurality of resting-stage and post-exerciseconditioned synchronized paired ECG-BCG signal sets collected from theindividual during a plurality of spaced apart testing periods.
 40. Amethod according to claim 38, wherein the plurality of synchronizedpaired ECG-BCG signals selected from the database comprise a pluralityof resting-stage and post-exercise conditioned synchronized pairedECG-BCG signal sets collected from a plurality of individuals.
 41. Adevice configured for concurrently receiving, conditioning, andprocessing at least two pluralities of physiological signals from anindividual, and additionally configured for synchronizing the at leasttwo pluralities of physiological signals and transmitting a synchronizedset of physiological signals, the device comprising; a motherboard; atleast one electronic device configured to concurrently receive at leasttwo pluralities of physiological signals; a microprocessor configured toconcurrently and separately perform on the incoming signals, a pluralityof functions selected from the group comprising processing, analyzing,optimizing, and transforming said incoming signals; a software programconfigured to cooperate with the microprocessor, the software programprovided with a first algorithm configured for processing andsynchronizing data from the at least two physiological signals andproducing therefrom a synchronized paired signal set comprisingrepeating cycles, a second algorithm configured for detecting, marking,identifying and characterizing the individual wave components comprisingthe repeating cycles of one of the synchronized paired signal set, and athird algorithm configured for comparing, analyzing and characterizing aplurality of synchronized paired signal sets; a database configured forstoring therein pluralities of physiological signal sets, andpluralities of synchronized paired signal sets; and a graphical userinterface configured configured to enable an operator to input data intothe database, and to access signals and outputs stored therein thedatabase.
 42. A system according to claim 1, wherein the softwareprogram is provided with a at least one algorithm configured to firstly,detect and mark a selected reference peak in a cycle of the conditionedfirst plurality of signals, then secondly, detect and mark a selectedreference peak in a cycle of the conditioned second plurality ofsignals, then thirdly, synchronize the first reference peak and thesecond reference peak thereby synchronizing the conditioned firstplurality of signals and the conditioned second plurality of signals andproducing a synchronized paired signal set therefrom, said paired signalset storable in the database.
 43. A system according to claim 1, whereinthe software program is provided with a plurality of algorithms,wherein: a first algorithm is configured to firstly, detect and mark aselected reference peak in a cycle of the conditioned first plurality ofsignals, then secondly, detect and mark a selected reference peak in acycle of the conditioned second plurality of signals, then thirdly,synchronize the first reference peak and the second reference peakthereby synchronizing the conditioned first plurality of signals and theconditioned second plurality of signals and producing a synchronizedpaired signal set therefrom; and a second algorithm is configured forderiving, identifying, marking, and characterizing individual componentsof the synchronized signal wave pattern output, and producing an outputtherefrom, said output storable in the database.
 44. A system accordingto claim 1, wherein the software program is provided with a plurality ofalgorithms, wherein: a first algorithm is configured to firstly, detectand mark a selected reference peak in a cycle of the conditioned firstplurality of signals, then secondly, detect and mark a selectedreference peak in a cycle of the conditioned second plurality ofsignals, then thirdly, synchronize the first reference peak and thesecond reference peak thereby synchronizing the conditioned firstplurality of signals and the conditioned second plurality of signals andproducing a synchronized paired signal set therefrom; a second algorithmis configured for deriving, identifying, marking, and characterizingindividual components of the synchronized signal set, and producing anoutput therefrom, said output storable in the database; and a thirdalgorithm is configured for comparing the individual components of thesynchronized signal set derived by the second algorithm, with theindividual components of a synchronized signal set stored in thedatabase, and produced an output therefrom, said output storable in thedatabase.
 45. A system according to claim 4, wherein the output from thesecond algorithm characterizes post-stress individual components of thesynchronized signal set, and the individual components of thesynchronized signal set stored in the database characterize a restingstage.